Simultaneous multiple assays

ABSTRACT

A particle agglutination-based, stable kinetic method for simultaneously determining the concentrations of multiple analytes in a single fluid sample with the addition of a single reagent, that entails the use of a novel high resolution sheath flow cell, a novel optical flow particle analyzer (FPA), and unidirectional low angle forward light scattering from multiply-sized or refractive indexed, differently coated particles and their aggregates. Also disclosed are two embodiments of an instrument specifically designed to carry out the method of the invention.

This is a continuation-in-part of Ser. No. 07/702,302, filed May 20,1991, now abandoned.

FIELD OF THE INVENTION

This invention relates to quantitative assays for multiple analytes in asingle fluid sample of biological origin. More particularly, the presentinvention relates to optical analytical methods based on rates ofparticle agglutination.

BACKGROUND OF THE INVENTION

Broadly applicable, accurate, sensitive and automatable assays areneeded to monitor the presence and quantity of biological materialspresent in complex body fluids of patients at micromolar to picomolarconcentrations in order to aid in diagnosis and therapy of disease.

Various methods utilized in the past, including liquid and gaschromatography, mass spectrometry, and numerous bioassay techniques, aretime-consuming, costly and not readily automated.

Competitive protein binding assays such as radioreceptor assays andradioimmunoassays provided a major improvement in analytical sensitivityand productivity, but have the disadvantages of dealing with hazardousradioactive materials, and not being amenable to automation. Whileenzyme-linked and chemiluminescence-linked immunoassays and DNA probeassays have eliminated the hazardous radioactive materials, they havenot solved the problem of a lack of automatability.

In recent years, a number of particle-based immunoassays have beendeveloped to take advantage of the specificity of antibody reactions,while avoiding the complications of radiochemical labelling.Agglutination reactions involving bivalent antibodies and antigens orhaptens of clinical interest have been utilized in both visual andquantitative assays with a wide variety of bacteria, red blood cells orpolymer particles. Agglutination results from the growth of antibody(Ab)-antigen (Ag)-bridged particle aggregates to produce an extensivenetwork that can be detected. Agglutination can result by adding thespecific binding partner, either Ab or Ag, to the suspension ofparticles with immobilized Ab or Ag. At low concentrations of thespecific binding partner, small aggregates consisting of only a fewparticles are produced. Particle-based diagnostic tests are usuallybased upon the very specific interaction of Ag and Ab. Ab or Ag can beadsorbed on submicron-sized polystyrene particles, often called "uniformlatex particles". Bangs, L. B., Uniform Latex Particles Indianapolis:Seragen, 1984. These sensitized particles then act to amplify thevisibility of the Ab-Ag reaction that takes place when a samplecontaining the sought Ag or Ab is mixed with these appropriately coatedparticles.

Suspensions of polymer microparticles in the colloidal size range of0.02-100 μm diameter particles are available commercially. Theproperties of these particles are determined predominantly by thephysicochemical properties of their surfaces. A single polystyrene latexparticle is composed of a large number of individual polystyrenemolecules (>1000 even for a particle as small as 0.1 μm diameter) heldtogether by van der Waal's attractive forces. Each polymer molecule inthe particle has end functional charge groups that are usuallyhydrophilic and that originate from a fragment of the compound used asthe initiator of the polymerization. See, for a review, Seaman, G. V.F., "Physicochemical Properties of Latexes in Design of Latex Tests", inSeaman, G. V. F., ed., Applying Latex Based Technology in Diagnostics,Health & Science Commun., Washington, D.C., 1990, pp.1-19.

The usual form of polystyrene latex particles possesses sulfate chargegroups for stabilization, but a variety of other functional groups canbe introduced at the particle surface, such as hydroxyl, carboxyl,amine, and polymeric carboxylate groups. Such groups are particularlyadvantageous for binding to latex bead surfaces a wide variety ofligands and receptors.

Although, as noted above, sizes of polystyrene microspheres availablecommercially cover the range of 0.2 μm up to about 100 μm, the sizesused for serodiagnostic testing are predominantly in the range of 0.1 to1.0 μm diameter. Performance characteristics are all influenced byparticle size and monodispersity. Sedimentation under the force only ofgravity may occur with the larger diameter microspheres, although thisis not a major problem in the size ranges used in agglutination assays.

Uncoated latex particles form relatively stable hydrophobic suspensionsbecause of like charge on all microspheres. When coated with a ligandsuch as Ag or Ab, the particles form stable hydrophilic suspensionsremaining dispersed during storage, but aggregating when reacted with acomplementary cross-reacting anti-ligand. The ligands used to coat latexparticles are attached by one of three methods: (i) physical (passive)absorption; (ii) facilitated (forced) absorption; and (iii) covalentcoupling.

Latex agglutination tests can employ either agglutination or inhibitionof agglutination of particles. Conventional agglutination tests are usedfor the detection of Ab's or relatively high molecular weight Ag's,while agglutination inhibition tests are used principally for thedetection of low molecular weight Ag's and also some larger Ag's.

When optical instruments that measure transmitted, absorbed or scatteredlight are used, it is possible to estimate agglutination of coated latexparticles quantitatively and to develop sensitive particle immunoassays.The intensity of light scattered by particles dispersed in water varieswith the number of particles, their diameter, the wavelength of theincident light, the angle of the detector to the incident light andseveral other variables.

As agglutination starts, single particles first become doublets; thenumber of monomeric light-scattering particles drops dramatically, andthe apparent diameter of agglutinates increases rapidly. After thispoint, the changes in numbers and diameters are less rapid. An importantaspect of particle agglutination, disclosed in the present inventionbelow, is that scattered light intensity measured as a function of timecan be the basis for a very sensitive kinetic immunoassay.

Several methods for quantifying particle immunoassays have already beendevised. Instruments such as Coulter Counters® (Coulter Electronics,Hialeah, Fla.) that count numbers of particles or clumps of particles indiscrete channels have been used to follow agglutination. As theparticles of small size agglutinate, the signals disappear from onechannel and appear in higher channels. One can thus count singleparticles as they decrease in number or count clumps of newly aggregatedparticles as they increase.

One can use a nephelometer to follow scattered light directly or aspectrophotometer to measure change of "absorbance" of light (measurescattered light indirectly). Angular anisotropy or dynamic lightscattering or photon correlation spectroscopy are newer, even morepowerful techniques for measuring particle agglutination quantitatively.

As noted above, traditionally, optical instruments such as turbidimetersor nephelometers that rely upon light scattering differences betweenagglutinated and unagglutinated particles have been applied to theproblem of quantitating latex particle agglutination tests. Althoughsuch methods preserve the advantage of monitoring a homogeneous reactionmixture without the need for a separation step, they are satisfactoryonly for single tests and are not satisfactory for simultaneous,quantitative, multiple latex particle agglutination tests, which is thesubject of the present invention below.

Light scatter from bulk solution of aggregating or dissociatingimmunobeads can be used to provide quantitative measurements of analyteconcentrations. Turbidimeters measure light transmission through asuspension of particle aggregates, and nephelometers directly measurescattered light in specific directions. In both instances, light scatterfrom a mixed population of both aggregated and nonaggregated particlesis measured. See, e.g., the LPIA® nephelometer instrument of MitsubishiChemical Ind., Tokyo that is capable, however, of analyzing only oneanalyte at a time; Kapmeyer et al., U.S. Pat. No. 4,305,925 whichdiscloses a nephelometric method wherein two different particle sizesare used to enhance the useful range of a latex agglutinationimmunoassay of a single analyte; and Ziege et al., WO 90/08961 whodiscloses a nephelometric quantitative immunoassay which employscoordinated carrier particles composed of copolymeric materials for thedetection of a single analyte. There is no obvious way to extend theteachings of these patents to the use of a multiplicity of particlesizes to measure different analytes simultaneously.

It is well known that particles of different sizes, shapes andcomposition relative to the wavelength of light will scatter lightdifferently in different directions. M. Kerker, The Scattering of Lightand Other Electromagnetic Radiation, Academic Press, N.Y. 1969. It wouldbe theoretically appealing to attempt to use the different angularscattering patterns of different particles in bulk solution in order toperform simultaneous assays. In practice, however, there is so muchoverlap in the angular scattering patterns of different particles thatit becomes impossible to separate the results of one agglutinationreaction from another.

As will be detailed below, the present invention employs an instrumentfor its simultaneous, quantitative multiple assay method that is neitherturbidimetric nor nephelometric, but instead monitors light scatteredfrom single particles or particle aggregates rather tan from manyparticles in bulk solution, and belongs to the class of instrumentsknown as Flow Particle Analyzers (FPA).

Two types of FPAs have been used to detect particle aggregation bymonitoring the size of individual particles or aggregates thereof asthey flow individually through either an electronic or optical sensingzone. In the first type, particles and particle aggregates flow througha physically small, electronic sizing orifice, and in the second typethe particles and aggregates flow through a focused optical beam.Although these approaches have been applied to quantitative latexparticle agglutination assays (see below), neither has been successfullyapplied to the problem of simultaneous, quantitative multiple latex beadagglutination tests, and are limited to single tests or require complexsignals to measure multiple analytes in a single sample.

Although electronic flow-through orifices can detect size differencesamong a population of electrically insulating particles, there arecertain practical limits to using such devices in latex particleagglutination tests, due, in part, to the clogging of sensitive sizingorifices by high order aggregates unavoidably produced duringagglutination tests and by particulate sample impurities. Masson, P. L.et al., Methods in Enzymology, 74:106 (1981); Cohen, R., U.S. Pat. No.4,851,329. This limitation has prevented any routine, practical use ofelectronic sizing orifices in attempts to quantify latex particleagglutination tests.

As optical FPAs can use large bore capillary sensing chambers and,therefore, do not suffer from clogging as readily as do electronicdevices, they are the preferred mode for single particle analysisapproaches to quantitative latex particle agglutination assays,including immunoassays.

Optical FPAs that sense aggregate formation by the measurement offorward scattered light have been described by Masson et al. (ibid.),Masson et al. (U.S. Pat. No. 4,279,617), Cambiaso et al. (U.S. Pat. No.4,184,849), and Cohen et al. (ibid.). Although these known systems arequantitative and sensitive, they disclose only single analyte assays,they are not aggregation rate-based methods, and they do not disclosesimultaneous particle agglutination assays of multiple analytes in asingle sample.

The Masson and Cambiaso systems, above, which sense forward scatteredlight pulses from non-aggregated particles that pass through a focusedoptical beam and which set electronic windows so as to ignore lightpulses from aggregated particles, prefer the use of latex particles oftwo different sizes for agglutination, perhaps to lessen the effect thatan initial distribution of multiplets (non-specifically formed withoutan Ag-Ab reaction occurring) may have on the assay reaction. Uzgiris etal., U.S. Pat. No. 4,191,739.

If particles of only one size are used, then the initial distribution ofdimers, trimers and multimers must be taken into account when measuringthe additional dimers, trimers, etc. that are created by theimmunochemical process. On the other hand, if two differently sizedparticles are coated with the same immunochemicals needed to measure agiven analyte, and are mixed together at the time the immunochemicalreaction is run, then there will be no initial aggregates of the twosizes of particles. This may lessen the effect that an initialdistribution of multiplets may have on the immunochemical reaction (seedetailed description of the invention below).

While the use of different size particles are disclosed by Uzgiris etal., above, Masson et al., above, Cohen et al. above and Cambiaso etal., above, for single analyte testing by latex particle agglutinationmethods, none of these references disclose solutions to the problems ofsimultaneous multiple testing by latex particle agglutination. Indeed,the particle size recommendations made in these references are soincomplete that the inventions are unworkable even for single analytes.The present invention, as will be detailed below, is concerned with thespecific means by which particles of differing sizes or refractiveindices must be chosen and used in order to quantitatively monitorsimultaneous multiple latex particle agglutination reactions.

Cambiaso et al., above, discloses a method for using a cross reactiveantibody immobilized on one of the particle sizes and an antigen thatreacts with only one of the antibody sites on the other size particle inan inhibition immunoassay. Although it is stated that the immobilizedantigen gives specificity to the assay, and that, by choosing thecorrect immobilized antigen, an assay for that antigen in a patientsample can be carried out, this method specifically fails if one or moreof the cross-reacting analytes is present simultaneously with othercross-reacting antigens. Therefore, the Cambiaso et al. system cannot beused for simultaneous multiple testing.

Abbott et al., U.S. Pat. No. 4,521,521, discloses a method forquantitatively measuring a single analyte in a liquid sample bymeasuring the rate of aggregation of analyte-bound particles. Measuringperpendicular light scatter is preferred. Abbott et al. do not teach amethod of estimating multiple analytes simultaneously in the samesample, do not teach the use of different size or refractive indexparticles for each of multiple analytes in a single sample, and teachparticles bound to analyte rather than to a ligand as in the presentinvention.

Abbott et al. above also disclose an analytical instrument for use withtheir immunoassay method. This instrument is, however, completelydifferent in terms of concept, principle, design, electronics andoperation than the optical flow particle analyzers of the presentinvention described below. Abbott relates to a particle sizedistribution measuring instrument, wherein count values for eachparticle size relating to the same analyte are obtained. Abbott et al.accomplish this, not by using single channel analyzers to separate pulsesignals from a light detector into separate output signals or by using apeak detector means to sample peak height values of pulse signals from adetector and outputting corresponding peak height values, as are done inthe instrument embodiments of the present invention, but, instead, by acounter network comprising a threshold comparator, a monostablemultivibrator that generates a logic signal for each electrical pulsepassing the comparator, and a counter in which is incremented the logicsignals. The output of the threshold comparator equals the differencebetween the light detector pulse signal and a preset threshold level,and is not the output signal of the detector as is employed in thepresent invention. Further, the signals are representative of only asingle analyte. The Abbott circuit does not separate the pulse signalsfrom the detector, but merely triggers the comparator in an all-or-nonefashion when a preset threshold level is exceeded. Because largemultimers generate pulses of greater amplitude than do lower multimersor monomers, in the Abbott system the pulses from N-mer particles willexceed the thresholds of all channels and will increment all counters.These threshold circuits are clearly not single channel analyzers.Further, the threshold circuits of Abbott cannot sample peak heightvalues, as is done by the peak detector means disclosed below, butrather are merely triggered when the signal exceeds a threshold. Thesignal may exceed the present threshold value, and trigger the circuit,before reaching its peak height value. In addition, the output of thethreshold comparator is merely a pulse indicative of the fact that thepulse exceeded a threshold value; it provides no information as to thepeak height of the signal, which peak height sampling is integral to thepresent FPA.

Cannon KK, JP 1207663, refers to a flow particle latex agglutinationassay method and instrument for measuring multiple analytessimultaneously in a fluid sample. The patent employs particles coatedwith Ag or Ab specific for the Ab or Ag to be detected. Differentparticles may be of the same or different size. The method detectsanalytes by detecting light scatter in two directions, one of which issideways, and uses an end point measurement of aggregation rather than amore advantageous rate-based assay as in the instant invention.

Thus, although particle agglutination-based assay methods that use flowor static particle analytical instruments are known, there remains animportant need for a particle agglutination method capable of performingpanels of in vitro laboratory tests, including immunoassays, on asimultaneous basis. That is, it would be greatly advantageous if such asimultaneous test could be performed by adding a single reagentcombination to a single sample of a patient fluid sample without need tosubdivide this sample, in contrast to present methods that requiredivision of the patient sample, use of multiple reagents in multiplesteps and collation of results at a later time. This need is nowfulfilled by the invention described below.

SUMMARY OF THE INVENTION

The present invention comprises a novel quantitative, kinetic, particleagglutination method for simultaneously estimating the concentration ofmultiple analytes in an initial fluid sample that entails the use of anovel high resolution optical sheath flow cell, a single detector formeasurement of pulse signals from unidirectional low angle forward lightscatter from multiply-sized, differently-coated monomeric particles andtheir aggregated multimers, and a novel flow particle analyzer ("FPA")apparatus.

It is thus an object of this invention to disclose a method ofperforming analyses for multiple analytes in a single fluid sample,wherein measurement of a unidirectional low angle forward light scattersignature from monomeric and aggregated, multimeric polymeric particlesas a function of time is correlated with analyte concentrations in thefluid sample, each analyte being measured using a particle of uniquesize or refractive index and unique coating.

It is a further object of this invention to disclose rate-based methodsfor the determination of aggregation of multiple-sized polymericparticles, each different size of particle being used to estimate theconcentration of a different analyte in a liquid sample.

It is yet another object of this invention to disclose a method fordetermining an optimum range of particle diameters or refractive indicesfor use in the method of the invention.

It is still another object of this invention to describe simultaneousimmunoassays of multiple analytes in a fluid sample using the particleaggregation rate method of the invention.

It is yet another object of this invention to provide sheath-type flowcell and flow particle analyzer embodiments specifically designed forthe simultaneous multiple particle agglutination-based assay method ofthe invention.

These and other objects will become apparent to the reader by referenceto the detailed description of the invention, the examples and theappended claims below.

DESCRIPTION OF THE DRAWINGS

FIG. 1 shows flow particle analyzer-detected separations of monomersfrom dimers, trimers and higher multiplets.

FIG. 2 is a sketch of the sheath flow cell of the flow particle analyzerof the invention.

FIG. 3 illustrates sheath flow of particles through a flow cell.

FIG. 4 shows the general layout of the optical system employed in theinvention.

FIG. 5A depicts the electronic layout of the flow particle analyzer ofone embodiment of the invention.

FIGS. 5B-5E show an inset of pulse heights (B) and SCA Count Rate (C-E)for 3 populations of particles.

FIG. 6A shows the electronic layout of the flow particle analyzer of asecond embodiment of the invention. Also shown in FIG. 6B as an inset isa plot of the total number of events versus pulse heights for twopopulations of particles.

FIG. 7 shows the distribution of scattered light pulse heights obtainedfrom two polystyrene spherical particle populations, with and withoutsheath flow.

FIG. 8 shows a theoretical plot of mean scattered light intensity as afunction of particle diameter. Data was taken from monomer peakchannels.

FIG. 9 shows the spectra of pulse heights obtained for uncoated 3.22 μmpolystyrene latex particles.

FIG. 10 shows a plot of the mean pulse height verses particle size,using the monomer peak channel data from the experiment shown in FIG. 9.

FIG. 11 shows the results of the kinetic assay method of the inventionapplied to immunoglobulin IgA in the presence of IgG ( ), compared toIgA analyzed alone ( ).

FIG. 12 results of the kinetic assay of the invention applied toimmunoglobulin IgG in the presence of IgA ( ), compared to IgG analyzedalone ( ).

FIG. 13 shows relative dimer formation as a function of time during theapplication of the kinetic assay method and the sheath flow optical FPAsystem of the invention to the immunoassay of human thyroid stimulatinghormone (TSH) in human serum, at concentrations of TSH (in μIU/mL) of0.0 (∘), 1.0 ( ), 25 ( ), and 100 (□).

FIGS. 14A-14D show FPA-generated histograms showing monomer, dimer andtrimer populations after reaction of analyte IgA with polystyrenespheres of different monomeric sizes coated with anti-IgA antibody.Relative monomer diameters were 1.00 (A), 1.08 (B), 1.23 (C) and 1.46(D).

FIG. 15 shows a pulse height histogram showing the optical resolvabilityof monomers and dimers of three sizes of polystyrene microspheres. Inthe figure, M₁ and D₁ represent monomers and dimers of 1.05 μm spheres,M₂ and D₂ for 1.62 μm spheres, and M₃ and D₃ for 1.78 μm spheres.

FIG. 16 shows the kinetic curves generated by simultaneous multipleanalyses of IgA, IgE and TSH using the optical FPA of the invention.Ratios of dimer to monomer are plotted as a function of time. Actualanalyte concentrations for each curve are listed in Table 1 of Example4. In the experiment, there is a "zero" IgA control.

FIG. 17 is the same as in FIG. 16, except that there is a "zero" TSHcontrol.

FIG. 18 is the same as in FIG. 16, except that there is an IgE "zero"control.

DETAILED DESCRIPTION OF THE INVENTION

The present invention is a quantitative, kinetic, particle agglutinationmethod for simultaneously measuring the concentrations of severalanalytes in a single fluid sample. The method entails the use of a novelhigh resolution optical flow particle analyzer instrument whereindetection by a single light detector of unidirectional low angle forwardlight scatter from differently sized and/or refractive indexed coatedmonomeric particles and their multimeric aggregates, is the basis of astable kinetic method designed for simultaneous assays of multipleanalytes in a single sample. The expressions "particles", "spheres","microspheres" and "beads" are used interchangeably herein and areintended to refer to polymeric (e.g., latex, polystyrene) sphericalparticles of generally uniform diameter and refractive index relative tothe surrounding medium.

Light Scatter

Single spherical particles scatter incident light according to thefollowing parameters: (a) intensity of incident light; (b) diameter ofthe particle; (c) wavelength of the incident light; (d) refractive indexof the particle; (e) refractive index of the surrounding medium; and (f)observation (scattering) angle. Theoretical analyses of light scatteringfrom single spherical particles are available using these parameters. M.Kerker, 1969, above.

Light scattering from aggregates of spherical particles of differentsize (i.e., 2-mer, 3-mer ... n-mer) depends, not only upon the aboveparameters, but also upon the orientation of the aggregate in theoptical beam and the specific configuration of the aggregate. Forexample, trimers can exist in a linear chain or in a triangularconfiguration. The enormous number of combinations of higher orderaggregate configurations makes a practical computational analysisimpossible. The description of the present invention relies, therefore,on a combination of theoretical and experimental observations.

Light scatter pulse heights or integrated pulse areas are not linearlyrelated to the volume or any other simple measure of cluster size.

Particles of a single size and shape can be resolved with high precisionin an FPA. For "exact" spherical particles in the 1-10 μm range ofdiameters, it is common to have FPAs with 1.5% distribution widths oflight scatter pulse heights. In other words, one can distinguish 1.00 μmparticles from 1.01 μm particles (assuming that the digital electronicshas a compatible resolving power). Thus, doublet (2-mer), triplet(3-mer) and higher multiplet (n-mer) distributions may be visualizedelectronically according to the invention with a FPA (FIG. 1). Althoughbroadening of the multiplets may occur because of orientation effects,as the asymmetric clusters tend to be oriented by the sheath flow of thepresent method, this is minimal. The separation between multipletsbecomes narrower as the size increases because of the nonlinear sizecorrelation with pulse height.

The present invention uses spherical particles of different diameter ordifferent refractive index for each analyte to be assayed, and relies onthe ability of a flow particle analyzer to distinguish between particlesand particle aggregates of different size or refractive index. Only thefactors that affect size resolution in an optical flow particle analyzerlimit the number of simultaneous assays that can be performed by thisapproach. Two of such factors, particle positioning effects andnon-monotonic relationships between scatter pulse amplitude and particlesize, and means to deal with those effects and relationships, arediscussed below.

Size Resolution-Particle Positioning Effects

An optical flow particle analyzer provides a pulse of scattered lightwhen each single particle or aggregate passes through the incident lightbeam. Optical beams cannot be made completely uniform in lightintensity; therefore in order to achieve high size resolution, it isessential that particles and aggregates pass very nearly through thesame region of the optical beam. This problem is not addressed in thelatex particle agglutination flow particle analyzers described byMasson, P. L. et al., Methods in Enzymology, 74:106-139 (1981) and U.S.Pat. No. 4,279,617, Cambiaso et al, U.S. Pat. No. 4,184,849, or Cohen etal, U.S. Pat. No. 4,851,329. However, the present invention solves thisproblem by the use of "sheath flow".

In this sheath flow method, cells are centered in the flow by the use ofa second, concentric stream that constricts the stream of cells to anarrow cross section and centers the cell stream in the highestintensity and most uniform region of the focused light beam. W. Gohde,et al., "DNA Measurements on Sperm and Blood Cells of Genetically Normaland Abnormal Humans" in Flow Cytometry IV, Universitetsforlaget, Bergen,Norway, 1980, pp. 273-276, and H. Shapiro, Practical Flow Cytometry,Second Edition, Alan R. Liss, Inc., New York, pp. 74.

The present invention uses sheath flow as a first step to obtainingmaximum resolution in the light scatter signature of particles andparticle aggregates. FIG. 2 is a sketch showing the essential componentsof the sheath flow cell of the optical flow particle analyzer of theinvention. A sample is formed into a particle stream surrounded bysheath fluid in a flow cell. Incident light (e.g., narrow band laserbeam) impinges on the particles at right angles, and scattered light isproduced. FIG. 3 illustrates sheath flow in a downward direction.

FIG. 4 is a sketch showing the general layout of the operatively-linkedcomponents of the optical system of the FPA used in this invention. Themonomeric particle and particle aggregate-scattered light exiting fromthe sheath flow cell passes through a collection lens with central beamblocker, and impinges on a light detector. Suitable light detectors inaccordance with this invention include photodiodes, photomultipliers,phototransistors and photoresistors. Each monomeric particle or particleaggregate that passes through the focal region of the optical beamproduces a pulse of low angle forward scattered light that is receivedby a light detector.

Signals from the light detector may be analyzed in several ways;however, two advantageous embodiments of the present invention arepreferred. The first embodiment is primarily a hardware-based method,whereas the second embodiment is primarily a software-based method.

In a first embodiment (FIG. 5A), pulses from the light detector arepreamplified and monitored on an oscilloscope. Distinct populations ofpulses with mean pulse height V_(M) can be seen corresponding to eachparticle size and aggregate size (FIG. 5B). Single channel analyzers("SCA")(Canberra Industries, Inc., Meriden, Conn.), one for eachanalyte, operatively linked to the preamplifier, are used to setelectronic windows that pass a narrow range of pulse heights ±ΔV aroundeach distinct population mean pulse height V_(M). Pulses that passthrough each SCA are fed to separate inputs of an analog-to-digitalconverter ("ADC"), and then registered in a computer ("CPU"). Thecomputer monitors the rate of arrival of pulses from each SCA, andpresents this rate as a function of time. The count rate as a functionof time for each of the three populations used in this example is shownin FIG. 5C. Various characteristics of the several count rate versustime graphs can be correlated with analyte concentration. Thesecharacteristics include initial rates of change, maximum rates ofchange, maximum count rates, relative dimer formation with time,differences in dimer:monomer count ratios with time, and time intervals(see Examples 2 and 4 below). Embodiments in which a separatepreamplifier and an oscilloscope monitor are not used fall within thescope of this embodiment.

It should be emphasized that the use of three SCA units in FIG. 5 and inthe accompanying description is merely one application of thisembodiment of the invention. In other analytical applications, greateror fewer than three SCA units may be used depending on the number ofanalytes being simultaneously measured, as long as a different SCA isassigned to each unique coated monomeric particle corresponding to eachanalyte.

In the second embodiment (FIG. 6A), the SCA components are disabled andall pulses are fed from a preamplifier directly to an ADC which samplesthe peak height of each pulse. The peak height values are then passed onto a computer, CPU. The computer sorts the peak height values by sizeand arranges then in a histogram.

The aforementioned histogram may be smoothed, if desired. This is donepreferably by using a binomially-weighted moving average method. Thoseskilled in this art will know of other methods for smoothing histograms.In this preferred method, an interval of pulse height values along the"X" axis of the histogram is selected and binomial coefficients are usedto weight the corresponding "Y" axis entries (number of pulses observedat each pulse height). For example, if an interval of seven pulseheights is elected, the seven entry row of Pascal's triangle (or tableof binomial coefficients) is consulted and the number of pulses observedat each pulse height is multiplied by the corresponding entry in thePascal triangle. These products are summed and divided by the sum of theseven Pascal triangle entries. The resulting value is entered as the new"number of pulse heights" at the middle pulse height. It is the natureof Pascal's triangle that this method gives the middle entry thegreatest weight. The algorithm moves on by taking a new interval ofpulse heights shifted by plus one on the "X" axis. The binomialweighting is then applied to the next "middle" data point. In order toachieve high rates of data analysis, this smoothing routine is appliedto the entire histogram generally not more than twice. There isrelatively little danger in applying this particular routine more thantwice as the histogram does not become degraded throughover-application.

The peaks of the smoothed histogram are now easy to locate by a numberof maximum value methods. A pulse height interval is selected bracketingeach peak, and the total number of events are counted in that interval(equivalent to the area under the curve in FIG. 6B). This step takes theplace of using SCA-determined windows as in the first embodiment (seeFIG. 5). This "Total Number of Events" is divided by the adjustable timeperiod described above to yield a "Count Rate" The count ratecalculation is repeated at various times during the course of theparticle agglutination reaction, with count rates plotted as a functionof time, and the characteristics of these curves are used to determinethe analyte concentration corresponding to each peak. As in theabovedescribed hardware embodiment, these characteristics may includeinitial slope, maximum slope, maximum count rate, relative dimerformation with time, differences in dimer:monomer count ratio with time,and time intervals.

FIG. 7 shows the distribution of scattered light pulse heights obtainedfrom two polystyrene spherical particle populations with mean diametersof 1.6 μm and 2.03 μm, respectively. With sheath flow, the optical flowparticle analyzer clearly distinguishes the two populations that haveonly a 0.43 μm difference in diameter. However, without sheath flow, thedistributions overlapped, and were not readily distinguishable.

Sheath flow is useful in obtaining high resolution for fluorescencepulses in flow cytometry, regardless of the mass of fluorescent materialin the particle. However, the analogous statement is not true for lightscatter. I have determined that even with sheath flow, certain ranges ofparticle size are inherently non-resolvable. This result is notanticipated by prior art, and it is within the scope of the presentinvention to provide means for selecting those particle size ranges thatcan be used in conjunction with sheath flow to perform multiple assays.

Size Resolution--Non-monotonic relationship between light scatter pulseamplitude and particle size

A complete optical wave analysis based on the theory of Mie (M. Kerker,1969, above) shows that the scattered light pulse amplitude fromspherical particles of uniform refractive index is not a simplemonotonic function of particle diameter. This analysis shows thatstanding waves would be formed in spherical particles and would giverise to constructive interference for certain particle sizes (peaks inFIG. 8) and destructive interference for other particle sizes (valleysin FIG. 8). Constructive interference results in increased light scatterand destructive interference gives rise to decreased light scatter. Thetheoretical curve in FIG. 8 has been derived from an optical waveanalysis. Theoretical analyses of light scattering are alwaysapproximate; however, the present experimental analysis (FIG. 10 below)clearly shows these constructive and destructive interference effects.

Experimental data was obtained from a FPA and compared with thetheoretical curve in FIG. 8. The FPA had the following characteristics.The light source was a helium neon laser operating at a wavelength of632.8 nm and was focused to an astigmatic horizontal stripe with theapproximate dimensions of 250 μm in the horizontal direction and 10 μmin the vertical direction. A sheath flow system was used to align theparticles substantially in the central 10 μm of the beam focus. A lenswas used to collect scattered light in a unidirectional low angleforward direction (between approximately 2 degrees and 7 degrees withrespect to the optical axis of the system). Low angle forward scatter ishighly advantageous. The present data show it to produce anapproximately 100-fold better signal to noise ratio than right angle,i.e., perpendicular, scatter. Pulses of scattered light were detected bya photodiode, passed through an electronic preamplification stage, andthen registered by pulse height in a data analysis system describedabove.

Uncoated polystyrene latex particles (Polysciences, Inc., Warrenton,Pa.) were suspended in distilled water and passed through the FPA flowcell. Suspension in distilled water ensured that ion-induced aggregationof the uncoated particles did not occur. Spectra of pulse heights wereobtained for each particle size and displayed for analysis as shown inFIG. 9. A plot of the mean pulse height versus particle diameter wasmade (FIG. 10), and can be compared to the theoretical curve (FIG. 8).Generally good agreement was obtained between theory and experiment;however, a systematic trend toward lower experimental pulse heights thanhad been predicted by the theory was noted for large particle sizes(right end of curve of FIG. 10).

From this curve, it can be seen that there are certain ranges ofparticle diameters that give light scatter pulses that are notresolvable even when sheath flow is used. For example, under theparticular experimental conditions described in FIG. 10 above, particleswith diameters in the 2 μm to 3 μm range (curve valley) were notresolvable from one another. This was also the case for particles withdiameters in the range between 4.0 μm and 5.5 μm.

Generally, particles with diameters in the regions of steep slope inFIG. 10 are preferred for simultaneous assays because they are morereadily resolved (see, e.g., FIG. 7). It is preferred to use particlediameters in the range of 0.02 to 12 μm. It is highly preferred to useparticle diameters in the 0.5 to 7.0 μm range.

It is within the scope of this invention, and would not require undueexperimentation, to use the method and FPA of the invention describedabove in order to select optically-resolvable particles for use insimultaneous assay of particular multiple analytes. Generally, theprocedure involves suspending in an assay reagent solution appropriateto the particular analytes being estimated antibody-coated monomericspheres of different diameter or refractive index. The assay procedureof the invention is then carried out with each unique sphere, using theoptical FPA of the invention. After an appropriate reaction period,which typically begins at about three minutes after mixing of thereagents and continues to about 30 minutes, histograms are generatedshowing monomer, dimer and trimer populations as a function of voltage.By superimposing histograms (see, e.g., FIG. 14), optically resolvablesphere sizes are revealed by simple inspection.

Alternate to the above-described particle size selection method in whichcoated particles are used with an immunoassay reagent, uncoatedparticles may be suspended in a salt solution that causes slow dimer,trimer, n-mer formation (Reynolds, P. A., et al., Colloids and Surfaces,23:273-299 (1987)). For example, polystyrene spheres may be suspended in0.35M NaCl and stirred for ten minutes; samples drawn periodically arethen analyzed by the optical FPA system of the invention, and histogramsdeveloped.

The curve for light scattering pulse amplitude versus particle diameteris altered when changes are made in the refractive index of theparticles, the refractive index of the suspending fluid, the wavelengthof the incident light, or the angle of observation for scattered light.Optimal particle diameters for simultaneous assays must be determined asshown above for any given combination of the above parameters. Thepresent invention utilizes particles chosen from these optimal regionsin order to maximize the number of simultaneous assays that can beperformed.

Any chemical reaction that can couple two beads can be monitored by themethod of the invention. For example, multiple antigen-antibodyreactions, wherein antibodies are the analytes in the patient samplebeing assayed, may be assayed simultaneously on the same patient fluidsample by using beads of different diameters, each with a differentantigen coating containing an epitope to the antibody. Similarly, beadsmay be coated with an antibody directed against an epitope of an antigenanalyte.

The method of the invention is flexible. It may be used to measureeither agglutination or inhibition of agglutination of coated particle.Components of the reaction mixture may be added concurrently orsequentially. The method may also be applied to competition or sandwichsystems wherein differently coated particles compete for binding to ananalyte ligand in a competition assay.

It is within the scope of the method of the invention to detect beadaggregation in blood or plasma that is undergoing a clotting reaction.Such reactions are useful in measurements of hemostasis.

The ability to carry out multiple analyte assays, clotting assays andcell counts simultaneously and on the same instrument is a majoradvantage over current practice that would use three differentinstruments for this purpose. The method and FPA of the invention areideal for exploiting this kind of combination testing.

The following examples are presented merely to provide specificembodiments of this invention, and are not intended to provide anylimitations to the invention not set forth in the claims.

EXAMPLE 1 Simultaneous Independent Immunoassays for Two Analytes

A simultaneous immunoassay for human IgG and human IgA was performedusing the sheath flow optical FPA system shown above.

Two sizes of Polystyrene Microspheres® (Polysciences, Inc., Warrington,Pa. 18976-2590) were each suspended to 0.5% (w/v) in 20 mM HEPES buffer,pH 8.0. The 1.23 μm beads (coefficient of variation of diameter ofparticles ranged from 0.1% to 4.0%) were incubated with 22.5 μg/mLrabbit anti-human IgA antibody and the 2.05 μm beads were incubated with17.5 μg/mL rabbit anti-human IgG antibody (Jackson ImmunoresearchLaboratories, Inc., West Grove, Pa.) for 30 minutes. The antibody coatedbeads were then coated with 0.2% nonfat dry milk solids (CarnationCompany, Los Angeles, Calif.) for 15 minutes in order to blocknonspecific binding sites. Coated beads were washed by repeatedsuspension in storage buffer (1.5M NaCl containing 0.5% bovine serumalbumin and 0.1% NaN₃, pH 7.4), and centrifugation. Control beads werecoated with nonfat dry milk solids for 15 minutes and washed as above.

Electronic windows were set to monitor the count rate of monomers ofthese two bead sizes as they passed through the sensing zone of theanalyzer. The initial time rate of change (negative slope) of theinstantaneous count rate of monomers was measured and quantitativelyrelated to the concentration of analyte. A data analysis method was usedthat ignored the initial lag phase of the reaction which usually rangesbetween 3 and 3.5 minutes after mixing. During this agglutination lagphase, analyte diffuses rapidly to the beads but very few collisionshave yet occurred between beads, and detectable agglutination has notyet occurred. After the lag phase, the less mobile beads collide andagglutinate at a rate that depends on the analyte concentration.

The results of these experiments are summarized in FIGS. 11 (IgA aloneand simultaneously with IgG) and 12 (IgG alone and simultaneously withIgA). These curves show the initial rate of monomer decrease versusanalyte concentration for the two analytes alone and then together.There was no significant difference between the data taken when theanalytes were measured alone or simultaneously. It is concluded that thereactions remained independent of each other even when the twoimmunochemical reactions occurred in the same reaction mixture.

This independence can be traced directly to the use of sheath flow andthe use of different sized beads taken from the appropriate regions ofthe light scatter versus bead diameter curve (FIG. 10) or from thesuperimposed histograms of FIG. 14.

EXAMPLE 2 Kinetics of Dimer Formation in an Assay of Thyroid StimulationHormone in Human Serum

An immunoassay for human thyroid stimulating hormone (TSH) in humanserum was performed using the sheath flow optical FPA system describedabove.

Polystyrene spheres (Interfacial Dynamics Corp., Seattle, Wash.) of 1.62μm diameter were coated with anti-TSH monoclonal antibodies byincubating the spheres overnight in a solution of 100 mg/mL of antibodyin 10 mM HEPES buffer, pH 7.5. Coated spheres were recovered by briefcentrifugation, and washed three times in a 4-fold volume of 10 mM HEPESbuffer, pH 7.5, containing 0.1% (w/v) BSA and 0.01% NaN₃.

Coated spheres were then suspended in 20 mM glycine buffer, pH 9.3,containing 0.1% BSA, 0.01% NaN₃ and 300 mM NaI. This reagent was addedto an equal volume of standard human serum (OEM Concepts, Inc., TomsRiver, N.J.) containing known concentrations of human TSH, andcontinuously stirred. The initial concentration of monomeric spheres wasabout 5×10⁷ monomers/mL. Dimeric spheres, present as a result of themanufacturing and coating processes, were about 2% of the initialmonomer concentration. The concentrations of TSH in the reaction mixturewere 0.0 μIU/mL (control, ∘ in FIG. 13), 1.0 μIU/mL ( in FIG. 13), 25μIU/mL ( in FIG. 13), or 100 μIU/mL (□ in FIG. 13).

Reaction mixtures were sampled at intervals over the course of 15minutes from initiation of the reaction, and analyzed by an optical FPAsystem of the invention. Dimer count rates were measured either as rawcount rates from the dimer windows, or relative count rates obtained asa ratio of dimer to monomer count rates or dimer to hardware controlbead (no analyte) count rate. The relative dimer count rates ("RelativeDimers") for four different TSH concentrations are shown in FIG. 13.

Each analyte reaction curve (Relative Dimers v. Time) shows an initiallag phase with a low slope. Each curve also shows a phase in which theslope is maximal, following the lag phase. The time required to reach amaximum slope decreases with increasing analyte concentration. Themaximum slopes clearly increase with increasing TSH concentration. Themaximum percent dimers (or relative dimers) compared to the monomers isgreater with increasing analyte concentration, and the time necessary toreach this maximum increases with decreasing analyte concentration. Inaddition, the area under each curve increases with increasing TSHconcentration when integrated over the same time limits. It is importantto note that, although all of the aforementioned characteristics of thereaction curves are related to TSH concentration, none is necessarilylinearly related.

The count rate plots versus time illustrate characteristics that cannotaccurately be predicted by mathematical models. The nonmonotonicbehavior of the curves, especially at high analyte concentrations, issurprising and must be considered on an analyte-by-analyte basis. Forexample, the time at which a TSH reaction reaches a maximum dimer countrate is different than the time necessary for an IgE assay reaction(cf., Example 1) to reach its maximum dimer rate, even if the molarconcentrations of the analytes are the same. These differences must betaken into account in calculating the most useful plot characteristicsthat are related to analyte concentration.

The plot characteristics shown in FIG. 13 were not altered significantlywhen absolute or relative dimer count rates were obtained by: 1) sendingpulses from an SCA set to accept dimer pulse heights to an ADC and thento a CPU; 2) sending pulses from an SCA set to accept monomer count ratewhere the dimer count rate originated from a separate SCA, and combiningthese by CPU to form a ratio of dimer to monomer count rate; or 3)sending pulses from an SCA set to accept monomer pulse heights from 1.05μm hardware control particles to an ADC, and forming the ratio of dimerto hardware control particles count rates where, again, the dimer countrate originated from a separate SCA.

Similar reaction curves were produced when a peak detector analyzermeans was used with an ADC to form histograms of pulse heights via a CPU(software embodiment). In this embodiment, a CPU was used rather thanSCAs to bracket windows for the monomer and dimer populations, whethersmoothed or unsmoothed histograms were used. Repeated samplings of thereaction mixtures over 15 minutes produced reaction plots that were notdifferent than those shown in FIG. 13.

Precision in these experiments was affected by the number of particlesof each monomer counted, and by the stability of the FPA fluid flow ratewhen ratios of reacting dimers to reacting monomers or ratios ofreacting dimers to hardware control beads were not used.

EXAMPLE 3 Determination of Optical Resolvability of Coated PolystyreneSpheres

Four sizes of polystyrene spheres (referred to hereinafter as A, B, Cand D) (Polysciences, Inc.) were coated with anti-IgA antibody as inExample 1. Coated spheres were washed and nonspecific binding sitesblocked as described in Example 1.

Suspensions of each size of coated spheres were then reacted,separately, with a fixed concentration of IgA (1 mg/mL) for 15 minutes,using the kinetic method and FPA of the invention as described above.The relative monomeric diameters of the sphere prior to reaction withanalyte stood in the ratio of 1.00 (A), 1.08 (B), 1.23 (C) and 1.46 (D).Histograms showing monomer, dimer and trimer populations were generatedwith the optical FPA.

Referring to FIG. 14, superimposition of the four sets of curves revealsthat spheres A and B, spheres A and D and spheres C and D are opticallyresolvable, as the early reaction histogram yielded peaks that wereclearly distinguishable from each other. In contrast, spheres B and C,and spheres A and C are not optically resolvable because of overlappingmonomer and dimer peaks. According to this analysis, then, combinationsof spheres A and B, spheres A and D, and spheres C and D could clearlybe employed in a simultaneous assay of two analytes.

EXAMPLE 4 Simultaneous Assay of TSH, IgE and IgA in a Single Sample

A simultaneous multiple immunoassay was performed on threeanalytes--human TSH, IgE and IgA using the sheath flow optical FPAsystem described above.

Polystyrene spheres (Interfacial Dynamics) of diameter 1.05 μm, 1.62 μmand 1.78 μm were selected as being optically resolvable using thecriteria of Example 3. In this selection process, uncoated microsphereswere induced to aggregate slowly by stirring the particles in thepresence of 0.35M NaCl for ten minutes. The suspension was then analyzedby the sheath flow optical FPA system, and histograms were developed.The pulse height histogram is shown in FIG. 15. M₁, M₂ and M₃ in thefigure represent the three monomeric species, and D₁, D₂ and D₃ thethree dimeric species, of the 1.05 μm, 1.62 μm and 1.78 μm spheres,respectively.

Spheres were coated with antibodies as described in Examples 1 and 2.The 1.05 μm spheres were coated with anti-human TSH antibodies, the 1.62μm spheres with anti-IgE antibodies, and the 1.78 μm spheres withanti-IgA antibodies.

Human serum, stripped of TSH, IgE and IgA content (OEM Concepts, Inc.)was used as the vehicle for analytes TSH, IgE and IgA, which were addedto this serum in known concentrations (see Table 1).

The reaction solution was the same as described in Example 2. Theaforementioned serum standard solutions represented 10% (v/v) of thetotal reacting mixture.

The initial monomer concentration was 5×10⁷ /mL for each sphere size.Initial dimer concentrations were approximately 1.5% in each case.

All reaction mixtures were sampled by the FPA system over a period ofabout 20 minutes. Stirring of reaction mixtures is necessary forparticle aggregation to occur. Therefore, reactions did not continue inaliquots removed from the reaction mixture for FPA analysis.

In FIGS. 16 (Response to IgA), 17 (Response to TSH) and 18 (Response toIgE), TSH is expressed as μIU/mL, IgE is in IU/mL and IgA is in mg, μgor ng/mL. Actual concentrations in each experiment are shown in Table 1.

                  TABLE 1                                                         ______________________________________                                                                       TSH    IgE                                     FIG.   Curve Symbol                                                                              IgA         μIU/mL                                                                            IU/mL                                   ______________________________________                                        16      □                                                                             0             2      100                                                      500    ng/mL  1       25                                                      1      μg/mL                                                                             2      100                                   17      □                                                                             1      μg/mL                                                                             2      100                                                      500    ng/mL  1       25                                                      5      mg/mL  0      100                                   18      □                                                                             1      μg/mL                                                                             2      100                                                      500    ng/mL  1       25                                                      5      mg/mL  2       0                                    ______________________________________                                    

The standard kinetic curves of FIGS. 16-18 were generated by plottingthe changes in dimer:monomer ratio ("DELTA R") with time for each set ofanalyte concentrations.

Each reaction kinetic curve was clearly separable, and showed nodetectable "cross-talk." This was established as follows. Each "zero"analyte concentration was read in the presence of a high concentrationof the other two analytes. In FIG. 16, IgA is seen as being "zero", inFIG. 17, TSH was "zero", and in FIG. 18, IgE was "zero" (see Table 1 fordetails). As the "zero" curves showed no discernable slope, it can beconcluded that neither of the other two analytes, even at highconcentration, produced inter-assay interaction. At the extreme, whenIgA was present at over 10⁻⁵ M (5 mg/mL), the apparent TSH zero value inFIG. 17 () was no greater than about 10⁻¹² M, i.e., seven orders ofmagnitude lower than was the actual analyte concentration. Such arejection ratio is sufficient, even for the most extreme requirements ina clinical setting.

As described in detail above, various plot characteristics in FIGS.16-18 may be correlated with analyte concentrations in order to makethis experiment the basis of the simultaneous quantitative estimation ofTSH, IgA and IgE in a single fluid sample.

I claim:
 1. An optical flow particle analyzer for simultaneous assay ofmultiple analytes in a single fluid sample by a rate-based particleaggregating method, comprising:a) a light source; b) anoptically-defined viewing zone upon which viewing zone focused lightfrom said light source is incident; c) means for flowing through saidviewing zone a reaction mixture comprising said single fluid sample anda reagent comprising, for each of said multiple analytes, monomericcoated particles of a diameter or refractive index unique for each saidanalyte, such that each said particle of unique diameter or refractiveindex or aggregate thereof produces a pulse signal from unidirectionallow angle forward light scatter that is distinguishable optically from apulse signal from unidirectional low angle forward light scatterproduced by any other monomeric coated particle of unique diameter orrefractive index or aggregate thereof wherein each said unique coatedparticle is coated with a unique composition that corresponds and bindsspecifically to a corresponding analyte so as to form aggregating coatedparticle-analyte binding pairs, so that unique monomeric coatedparticles or aggregated multimers formed therefrom flowing through saidviewing zone produce discrete pulses of scattered light unique for eachsaid unique coated particle-analyte binding pair or aggregated multimerthereof; d) lens means for collecting said pulses of unidirectional lowangle forward scattered light; e) single light detector means forreceiving collected pulses of said unidirectional low angle forwardscattered light and converting said collected pulses into electricalpulse signals, each of said pulse signals being unique for each saidcoated particle monomer or each said aggregated multimer correspondingto different analytes; f) analyzer means for separating said electricalpulse signals into separate output signals, each of said separate outputsignals representative of a different analyte, wherein said analyzermeans comprises a plurality of single channel analyzers, each of saidsingle channel analyzers being dedicated to each said coated particlemonomer of unique diameter or refractive index, or aggregated multimerthereof, each of said unique monomers or multimers thereof correspondingto each of said multiple analytes, such that each of said single channelanalyzers monitors the pulse signals from each of said coated monomericparticles of unique diameter or refractive index, or aggregatedmultimers thereof, and such that each said dedicated single channelanalyzer passes as output signals, signals falling within predeterminedranges of signal values, said ranges differing for each subset of saidunique coated monomeric particles or aggregated multimers thereofcorresponding to each of said multiple analytes; and g) calculator meansfor calculating and correlating a rate of arrival of each of said outputsignals per unit time from said analyzer means with each said analyte.2. An optical flow particle analyzer of claim 1 wherein said lightsource comprises a laser beam generator.
 3. An optical flow particleanalyzer of claim 1, wherein said optically-defined viewing zone uponwhich focused light radiation is incident comprises a sheath flow cellfor aligning said flowing particles within a central portion of saidfocused light.
 4. An optical flow particle analyzer of claim 1, whereinsaid lens means comprises a collection lens with a central beam blocker.5. An optical flow particle analyzer of claim 1, wherein said lightdetector means comprises a light detector selected from the groupconsisting of photodiode, photomultiplier, phototransistor andphotoresistor detectors.
 6. An optical flow particle analyzer of claim1, further including amplifying means for preamplifying said electricalpulse signals from said single light detector means and applying saidpreamplified pulse signals to said analyzer means.
 7. An optical flowparticle analyzer of claim 6, wherein said amplifying means comprises apreamplifier.
 8. An optical flow particle analyzer of claim 6, furthercomprising monitor means for monitoring said preamplified signals.
 9. Anoptical flow particle analyzer of claim 6, wherein said monitoring meansfor monitoring said preamplified signals comprises an oscilloscope. 10.An optical flow particle analyzer of claim 6, wherein said plurality ofsingle channel analyzers receives preamplified signals and passes asoutput signals preamplified signals falling within said predeterminedranges of signal values.
 11. An optical flow particle analyzer of claim1, further comprising peak detector means for converting said outputsignals into digital signals representative of peak heights of saidoutput signals.
 12. An optical flow particle analyzer of claim 11,wherein said peak detector means comprises an analog-to-digital signalconverter.
 13. An optical flow particle analyzer of claim 1, whereinsaid calculator means comprises a computer.
 14. An optical flow particleanalyzer of claim 13, wherein said computer includes means forrepetitively monitoring the rate of arrival of each output signal fromsaid analyzer means, means for repetitively plotting these rates as afunction of time during aggregation reactions of said assay, and meansfor determining each analyte concentration based on characteristics ofeach said plot, wherein said plot characteristics are selected from thegroup consisting of initial rates of change, maximum rates of change,maximum count rate, relative dimer formation with time, differences indimer:monomer ratio with time, and time intervals.
 15. An optical flowparticle analyzer for simultaneous assay of multiple analytes in asingle fluid sample by a rate-based particle aggregating method,comprising:a) a light source; b) an optically-defined viewing zone uponwhich zone focused light from said light source is incident; c) meansfor flowing through said viewing zone a mixture comprising said singlefluid sample and a reagent comprising, for each of said multipleanalytes, particles of a diameter or refractive index unique for eachsaid analyte, such that each said particle of unique diameter orrefractive index or aggregate thereof produces a pulse signal fromunidirectional low angle forward light scatter that is distinguishableoptically from a pulse signal from unidirectional low angle forwardlight scatter produced by any other particle of unique diameter orrefractive index or aggregate thereof, wherein each said unique particleis coated with a unique composition that corresponds and bindsspecifically to a corresponding analyte so as to form aggregating coatedparticle-analyte binding pairs, so that monomeric particles oraggregates formed therefrom flowing through said viewing zone producediscrete pulses of scattered light unique for each said unique coatedparticle-analyte binding pair or aggregates thereof; d) lens means forcollecting said pulses of unidirectional low angle forward scatteredlight; e) single light detector means for receiving collected pulses ofsaid unidirectional low angle forward scattered light and convertingsaid pulses into electrical pulse signals, each of said pulse signalsbeing unique for said particle monomers or aggregates thereofcorresponding to different analytes; f) peak detector means for samplingthe peak height values of said electrical pulse signals and outputtingpeak height signals corresponding thereto; and g) calculator means forcorrelating each said peak height signal with each said analyte.
 16. Anoptical flow particle analyzer of claim 15, wherein said light sourcecomprises a laser beam generator.
 17. An optical flow particle analyzerof claim 15, wherein said optically-defined viewing zone upon whichfocused light radiation is incident comprises a sheath flow cell thataligns said flowing particles in a central portion of said focusedlight.
 18. An optical flow particle analyzer of claim 15, wherein saidlens means comprises a collection lens with a central beam blocker. 19.An optical flow particle analyzer of claim 15, wherein said single lightdetector means comprises a light detector selected from the groupconsisting of photodiode, photomultiplier, phototransistor andphotoresistor detectors.
 20. An optical flow particle analyzer of claim15, further comprising an amplifier means for preamplifying electricalpulse signals from said single light detector means and outputting saidpreamplified electrical pulse signals to said peak detector means. 21.An optical flow particle analyzer of claim 15, wherein said peakdetector means comprises an analog to digital converter that samples thepeak height of each said electrical pulse signal and converts said peakheight into a digital peak height signal.
 22. An optical flow particleanalyzer of claim 15, wherein said calculator means comprises acomputer.
 23. An optical flow particle analyzer of claim 22, whereinsaid computer includes means for sorting said peak height values by sizeinto histograms, means for selecting peak height intervals bracketingeach peak of said histograms, means for repetitively calculating a countrate of each said peak height interval during particle aggregatingreactions, means for plotting each of said count rates as a function oftime, and, means for determining each said analyte concentrationcorresponding to each said peak based on characteristics of said plot,wherein said plot characteristics are selected from the group consistingof initial rates of change, maximum rates of change, maximum count rate,relative dimer formation with time, differences in dimer:monomer ratiowith time, and time intervals.
 24. An optical flow particle analyzer ofclaim 23 further including means for smoothing said histograms.